One aspect of the present subject matter provides an imaging method including: receiving a trigger signal; after a period substantially equal to a trigger delay minus an inversion delay, applying a non-selective inversion radiofrequency pulse to a region of interest followed by a slice-selective reinversion radiofrequency pulse to a slice of the region of interest of a subject; and after lapse of the trigger delay commenced at the cardiac cycle signal, acquiring a plurality of time-resolved images of the slice of the region of interest from an imaging device.

Image reconstruction methods for multi-slice and multi-contrast magnetic resonance imaging with complementary sampling schemes are provided, comprising: data acquisition using complementary sampling schemes between slices or/and contrasts) in spiral imaging or Cartesian acquisition; joint calibrationless reconstruction of multi-slice and multi-contrast data via block-wise Hankel tensor completion.

The present disclosure provides a system and method for image data acquisition. The method may include obtaining image data of a subject including a first type of tissue and a second type of tissue. The method may include determining, based on the image data of the subject, a target portion including at least a portion of at least one of the first type of tissue or the second type of tissue. The method may include determining, based at least in part on the target portion represented in the image data, a scan mode corresponding to the target portion. The method may include causing an imaging device to acquire, based on the scan mode, image data of the target portion.

An implantable array suitable for being placed in anatomic tissue of a human or animal body is provided. The implantable array has a substrate and a reference structure, the reference structure being formed by a number of notches arranged in at least one outer edge of the substrate, the reference structure defines a spatial relationship with predefined points of the array.

In a method for improving the contrast of magnetization-transfer-prepared magnetic resonance imaging (MRI), an acquisition scheme comprising a plurality of inversion-recovery (IR)-imaging modules in an interleaved arrangement is selected, a number of magnetization-transfer (MT)-preparation modules is selected, a pulse sequence is generated by arranging at least one MT-preparation module of the number of MT-preparation modules between two successive IR-preparation modules of the interleaved IR-imaging modules or in front of the first IR-preparation module of a group of interleaved IR-imaging modules, and the pulse sequence for an MRI examination is applied or saved. Each IR-imaging module may include an IR-preparation module and a slice acquisition module.

A method for determining a brain age, the method comprising the following: providing a brain age determining convolutional neural network (CNN) (200); training the CNN (200) to determine the brain age based on a plurality of sets of input data comprising magnetic resonance imaging (MRI) scans of a brain, the set comprising at least two types of MRI volumes, wherein the at least one type of brain tissue on the first type of the MRI volume is represented by a different contrast with respect to other tissues than on a second type of the MRI volume; and performing an inference process using the trained CNN (200) to determine the brain age based on the set of input data comprising magnetic resonance imaging (MRI) scans of a brain, the set comprising at least the two types of the MRI volumes as used for the training.

A 3D model of AC electrical conductivity (at a given frequency) of an anatomic volume can be created by obtaining two MRI images of the anatomic volume, where the two images have different repetition times. Then, for each voxel in the anatomic volume, a ratio IR of the intensity of the corresponding voxels in the two MRI images is calculated. This calculated IR is then mapped into a corresponding voxel of a 3D model of AC electrical conductivity at the given frequency. The given frequency is below 1 MHz (e.g., 200 kHz). In some embodiments, the 3D model of AC electrical conductivity at the given frequency is used to determine the positions for the electrodes in TTFields (Tumor Treating Fields) treatment.

The invention relates to a method of MR imaging. It is an object of the invention to provide an improved B.sub.1 mapping method that is less affected by T.sub.1 relaxation. The invention proposes that a first stimulated echo imaging sequence (25) is generated comprising at least two preparation RF pulses (α) radiated during a first preparation period (21) and a sequence of reading RF pulses (β) radiated during a first acquisition period (22) temporally subsequent to the first preparation period (21). A first set of FID signals (I.sub.FID) and a first set of stimulated echo signals (I.sub.STE) are acquired during the first acquisition period (22). A second stimulated echo imaging sequence (27) is generated comprising again at least two preparation RF pulses (α) radiated during a second preparation period (21) and a sequence of reading RF pulses (β) radiated during a second acquisition period (22) temporally subsequent to the second preparation period (21). A second set of FID signals (I.sub.FID) and a second set of stimulated echo signals (I.sub.STE) are acquired during the second acquisition period (22). The first and second sets of FID signals (IFID) have different T.sub.1-weightings and/or the first and second sets of stimulated echo signals (I.sub.STE) have different T.sub.1-weightings. A B.sub.1 map indicating the spatial distribution of the RF field of the RF pulses is derived from the acquired first and second sets of FID (I.sub.FID) and stimulated echo (I.sub.STE) signals, wherein the different T.sub.1-weightings are made use of to compensate for influences on the B.sub.1 map caused by T.sub.1 relaxation. Preferably, either the first or the second preparation period (21) is preceded by an RF inversion pulse to obtain the different T.sub.1-weightings. Moreover, the invention relates to an MR device (1) and to a computer program for an MR device (1).

The disclosure relates to a fast susceptibility imaging techniques for performing flow compensations in the slice, phase, and frequency encoding directions for the central echo of a plurality of echoes excited each time in interleaved echo planar imaging (iEPI). The echo data for which flow compensations have been performed may be collected, and susceptibility-weighted imaging (SWI) performed for collected echo data. The fast susceptibility imaging techniques may reduce scan time.

The invention relates to a method of MR imaging of an object (10) positioned in an examination volume of a MR device (1). It is an object of the invention to enable fast spiral MR imaging with a defined T2 contrast. The method of the invention comprises the following steps: —generating a number of spin echoes by subjecting the object (10) to one or 5 more shots of an imaging sequence, each shot comprising an RF excitation pulse (21) followed by a number of RF refocusing pulses (22), wherein modulated readout magnetic field gradients (23, 24) are applied in each interval between successive RF refocusing pulses (22), —acquiring MR signal data, wherein each spin echo is recorded along a spiral trajectory (31-33, 41-43) in k-space which winds around the k-space origin with varying radial distance, wherein the trajectory (31, 41) of at least one spin echo has a different rate of variation of the radial distance at least in a central k-space region compared to the trajectories (32, 33, 42, 43) of the other spin echoes, and—reconstructing an MR image from the acquired MR signal data. Moreover, the invention relates to an MR device (1) and to a computer program for an MR device (1).